US10383636B2

US10383636B2 - Embolization device and a method of using the same

Info

Publication number: US10383636B2
Application number: US15/918,869
Authority: US
Inventors: Thomas J. Fogarty; Michael J. Drews; D. Bruce Modesitt; Neil D. HOLMGREN; David B. Willis
Original assignee: Individual
Current assignee: Endologix LLC
Priority date: 2002-11-12
Filing date: 2018-03-12
Publication date: 2019-08-20
Anticipated expiration: 2022-11-12
Also published as: US20190321051A1; US20040210249A1; US9005235B2; US7481821B2; WO2004043241A3; US20180199946A1; US9913651B2; US20140088690A1; AU2003290869A1; US20090105748A1; US10842497B2; US20150182228A1; US20120303108A1; US8562636B2; US8262686B2; WO2004043241A2; US9629636B2; US20160113658A1; AU2003290869A8; US20210145446A1

Abstract

Non-expandable space-occupying devices for treating voids within the body are disclosed. The devices can have multiple non-expandable space-occupying elements connected to a flexible leader. Methods of making and using the devices are also disclosed.

Description

CROSS-REFERENCE TO RELATED APPLICATION

This application is a continuation of U.S. application Ser. No. 14/990,666, filed Jan. 7, 2016, which is a continuation of U.S. application Ser. No. 14/657,888, filed Mar. 13, 2015, now issued U.S. Pat. No. 9,629,636, which is a continuation of U.S. application Ser. No. 14/058,986, filed Oct. 21, 2013, now issued U.S. Pat. No. 9,005,235, which is a continuation of U.S. application Ser. No. 13/569,348, filed Aug. 8, 2012, now issued U.S. Pat. No. 8,562,636, which is a divisional of U.S. application Ser. No. 12/340,483, filed Dec. 19, 2008, now issued U.S. Pat. No. 8,262,686, which is a continuation of U.S. application Ser. No. 10/293,139, filed Nov. 12, 2002, now issued U.S. Pat. No. 7,481,821, each of which are incorporated by reference herein in their entireties.

BACKGROUND OF THE INVENTION 1. Field of the Invention

The present invention relates generally to a device for filling and/or stabilizing the void within an anatomical organ of the body, particularly within the vasculature, and methods for making and using the device.

2. Description of the Related Art

An aneurysm is an abnormal dilatation of a biological vessel. Aneurysms can alter flow through the affected vessel and often decrease the strength of the vessel wall, thereby increasing the vessel's risk of rupturing at the point of dilation or weakening. FIG. 1 illustrates an abdominal aorta 2 with a sacular aneurysm 4 having an aneurysm wall 6. FIG. 2 illustrates the abdominal aorta 2 with a vascular prosthesis 8 implanted to treat the aneurysm 4, a common aneurysm therapy. Vascular grafts and stent-grafts (e.g., ANEURX® Stent Graft System from Medtronic AVE, Inc., Santa Rosa, Calif.) are examples of vascular prostheses used to treat aneurysms by reconstructing the damaged vessel.

With the prosthesis 8 implanted, an aneurysm sac 10 is defined by the volume between the prosthesis 8 and the aneurysm wall 6. The sac 10 is often filled, partially or completely, with thrombi 12. The thrombi 12 can be partially removed prior to deploying the prosthesis 8. Whether the thrombi 12 are removed, gaps exist between the remaining thrombi 12 or the aneurysm wall 6 and the prosthesis 8, and even when thrombus is present, it can be soft and non-structural. The prosthesis 8 can dislodge or migrate due to the poor fit caused by these gaps and shrinkage of the sac 10 that occurs after the implantation of the prosthesis 8, either acutely due to sizing issues, or over time due to reformation of the sac 10. To reduce the risk of prosthesis dislodgement and migration, the sac 10 can be filled to stabilize the anatomy adjacent to the prosthesis 8 resulting in better efficacy of the prosthetic treatment.

A sac filler, or stabilizer, can be introduced to the sac 10 by trans-graft, trans-collateral, trans-sac, or endoluminal procedures. The trans-graft procedure introduces the sac filler through an opening in the prosthesis 8, as shown by arrows 12. The trans-collateral procedure, shown by arrows 16, introduces the sac filler through a collateral vessel 18 under fluoroscopic guidance that is in direct communication with the sac 10. The trans-sac procedure, often performed laparoscopically, introduces the sac filler through a puncture in the wall 6 of the aneurysm, as shown by arrows 20. The endoluminal procedure introduces the sac filler through the vessel that has the aneurysm 4, as shown by arrows 22, but within the space between the prosthesis and the vessel wall. The trans-graft, trans-collateral and endoluminal procedures are often performed as minimally invasive, entirely endovascular procedures.

It is desirable for a stabilizing element or sac filler to conform to the available space within the sac 10 by operation of the geometry of the device (e.g., by nesting or coiling) and/or by any coatings or materials utilized to promote fusing or other coagulative effect.

U.S. Pat. No. 6,146,373 to Cragg et al. discloses a catheter system and method for injecting a liquid embolic composition and a solidification agent directly into a sac. Cragg et al. teach the use of organic solvents such as DMSO, ethanol and others injected directly in the aneurysm. Cragg et al. teach that these solvents can be toxic to tissue and may cause vascular spasms. Using liquid-solidifying agents in active vessels also carries a high risk that the agents will flow downstream creating emboli or flow into collateral vessels (e.g., lumbar arteries), which may lead to paralysis or other adverse events.

U.S. Pat. No. 4,994,069 to Ritchart et al., U.S. Pat. No. 5,133,731 to Butler et al., U.S. Pat. No. 5,226,911 to Chee et al., and U.S. Pat. No. 5,312,415 to Palermo disclose examples of thrombogenic microcoils, common aneurysm treatments. The microcoil must be tightly packed into the aneurysm to minimize shifting of the microcoils. Shifting of the microcoil can lead to recanalization of the aneurysm. Another disadvantage of microcoils is that they are not easily retrievable. If a coil migrates out of the aneurysm, a second procedure to retrieve the coil and move the coil back into place, or replace the coil, might be necessary.

U.S. Pat. Nos. 6,238,403 and 6,299,619, both to Greene, Jr. et al., disclose an embolic device with expansible elements and methods for embolizing a target vascular site with the device. The device taught by Greene Jr. includes a plurality of highly-expansible elements disposed at spaced intervals along a filamentous carrier. The expansion of the device after deployment reduces the volumetric precision with which the sac can be filled. If the volume of the expanded device is too large, the device can press against the inner side of weakened aneurysm wall and outer side of prosthesis, altering flow within the prosthesis and increasing the risk of rupture of the aneurysm. If the volume of the expanded device is too small, the prosthesis can still alter its position and dislodge or migrate.

There is thus a need for a device and method that can precisely occlude a known sac volume with minimal displacement of the device over time. There is also a need for a device that can be deployed to the sac 10 while simultaneously minimizing toxicity, embolism risk, and other disadvantages previously associated with existing aneurysm sac fillers.

BRIEF SUMMARY OF THE INVENTION

One embodiment of the disclosed device is a vascular embolization device having a flexible leader connected to at least one non-expandable, space-occupying element. The elements can be made, for example, from collagen and/or a polymer such as polypropylene. The device can also have a radiopaque agent fixed to or integrated with the device. Furthermore, the device can be coated or infused with a therapeutic and/or diagnostic agent.

Another embodiment of the disclosed device is a vascular embolization device having a leader made from a flexible material and a space-occupying element connected to the leader. The element has a first component secured to a second component. The element can also be slidably connected to the leader, for example, by a ferrule.

Yet another embodiment of the disclosed device is a vascular embolization device having one or more cylindrical space-occupying elements connected by flexible helical segments. When fully extended, the element has a cross-sectional width to cross-sectional height ratio of equal to or greater than about 1.5:1. The cross-sectional width-to-height ratio can also be equal to or greater than 4:1.

A further embodiment of the disclosed device is a vascular embolization device having a first space-occupying element having a first male interference-fit piece, and a second space-occupying element having a first female interference-fit piece. The first male interference-fit piece and the first female interference-fit piece attach to impede removal of the first male interference-fit piece from the first female interference-fit piece.

Yet another embodiment of the disclosed device is a vascular embolization device. The device has a first space-occupying element comprising a body and a first female interference-fit piece. The device also has a second space-occupying element comprising a body and a second female interference-fit piece. Furthermore, the device has a leader comprising a first male interference-fit piece on a first end and a second male interference-fit piece on a second end. The first male interference-fit piece attaches to the first female interference-fit piece attach and the second male interference-fit piece attaches to the second female interference-fit piece.

A method is also disclosed for placing a space-occupying device or a plurality of space-occupying devices, such as the embolization devices disclosed herein, within a void. For example, a catheter having a distal exit is placed at a vascular site. A vascular embolization device is then passed through the catheter and the distal exit and deployed into the vascular site. The device has a flexible leader and at least one non-expandable, space-occupying elements connected to the leader. The method can include selecting a device or devices having the proper volume so that the device(s) is large enough to substantially fill the void, such as an aneurysmal sac within the vasculature, yet small enough to prevent substantial alteration of the natural fluid flow through an adjacent element, for example a vascular prosthesis implanted at or near the vascular site. Furthermore, the method of the present invention may provide for the removal of material within the void, such as the removal of thrombus from the aneurysmal sac and treatment with therapeutic agents prior to, or in conjunction with, the placement of the space-occupying elements.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 not the invention, illustrates an aneurysm.

FIG. 2 not the invention, illustrates a vascular prosthesis implanted within an aneurysm and procedures for filling the aneurysm sac.

FIG. 3a illustrates an embodiment of the embolization device.

FIG. 3b illustrates a portion of the embolization device of FIG. 3 a.

FIG. 4 is a cross-sectional view of an embodiment of the leader and the space-occupying element.

FIG. 5 illustrates an embodiment of the leader and the space-occupying element of FIG. 4.

FIG. 6 illustrates an embodiment of the first section of the space-occupying element.

FIG. 7 illustrates an embodiment of the space-occupying element of FIG. 6.

FIG. 8 illustrates an embodiment of the first section of the space-occupying element.

FIG. 9 illustrates an embodiment of the space-occupying element of FIG. 8.

FIGS. 10 and 11 illustrate segments of embodiments of the embolization device.

FIGS. 12a-c and 13 illustrate embodiments of the embolization device.

FIG. 14 illustrates a segment of an embodiment of the embolization device.

FIG. 15 illustrates an embodiment of the method of implanting the embolization device.

FIG. 16 is a cut-away view of a catheter carrying an embodiment of the embolization device.

FIGS. 17 and 18 illustrate embodiments for the drivers used to deploy the embolization device.

FIG. 19 illustrates an embodiment of the slider from the driver.

FIG. 20 illustrates an embodiment of the connector.

FIG. 21 illustrates an embodiment of the connector in an unlocked configuration.

FIG. 22 is a cross-sectional view of the connector of FIG. 21.

FIG. 23 illustrates the connector of FIG. 21 in a locked configuration.

FIG. 24 is a cross-sectional view of the connector of FIG. 23.

DETAILED DESCRIPTION

FIG. 3a illustrates an embodiment of a vascular embolization or occlusion device 24 having a flexible leader 26 that can be connected to a first non-expandable space-occupying element 28 and a second non-expandable space-occupying element 30. Additional non-expandable space-occupying elements 32 can also be connected to the leader 26 and provided in various lengths, depending on the typical volume of the sac 10 to be filled. The leader 26 can pass through the

elements

28, 30 and 32. The leader 26 can be fixed to the

elements

28, 30 and 32, or the

elements

28, 30 and 32 can slide freely over the leader 26. As illustrated in FIG. 3b , the leader 26, even if secured within an

element

28, 30, or 32, can flex and bend within each

element

28, 30 or 32, or between the

elements

28, 30 and 32.

The leader 26 can be a suture, preformed resilient structure, poppet, wire, fiber, monofilament, rail, or a woven thread or other combination thereof. The leader 26 can be completely separate and discrete from the

elements

28, 30 and 32. The leader 26 can be made from polymer, for example polyester (e.g., DACRON® from E. I. du Pont de Nemours and Company, Wilmington, Del.), polypropylene, polytetrafluoroethylene (PTFE), expanded PTFE (ePTFE), nylon, extruded collagen, silicone and combinations thereof. The leader 26 can have a leader diameter 34 from about 0.050 mm (0.0020 in.) to about 1.3 mm (0.050 in.), more narrowly from about 0.2 mm (0.006 in.) to about 0.25 mm (0.010 in.). A leader span 36 between the

elements

28 and 30 can be from about 0 to about 2 times an element outer diameter 38, more narrowly from about 0.5 to about 1 time the element outer diameter 38. A total device length 40 from one end of the device 24 to the other can be any length desired, for example about 30 cm (1 ft.).

The

elements

28, 30 and 32 can be spherical, cylindrical, or an approximation thereof. The

elements

28, 30 and 32 can be made from any of the materials disclosed above for the leader 26 as well as collagen, glass, polylactic acid (PLA), poly(lactic-co-glycolic acid) (PLGA), polyglycolic acid (PGA), other bioabsorbable material, polyurethane, polyethylene, or metal, for example stainless steel, titanium or nitinol. The element outer diameter 38 can be more than about 0.1 mm (0.005 in.) of the leader diameter 34. The element outer diameter 38 can be larger than about 0.25 mm (0.010 in.) less than an inner diameter of a catheter through which the device 24 is deployed. The element outer diameter 38 can also be larger than about 2.0 mm (0.079 in.), more narrowly larger than about 2.7 mm (0.11 in.). An element length 42 can be in the aforementioned ranges for the element outer diameter 38.

A device volume can be determined by calculating the total volume of the

elements

28, 30 and 32 added to the total volume of the leaders 26. If the leader 26 or the

elements

28, 30 and 32 are made from bioabsorbable materials, the reduction of device volume over time can be accounted for when calculating device volume. The device volume can be from about 20 cc (1.2 in.³) to about 200 cc (12.2 in.³), more narrowly from about 60 cc (3.7 in.³) to about 100 cc (6.1 in.³).

FIGS. 4 and 5 illustrate an embodiment of the element 28 with the leader 26. The

elements

30 and 32 can have embodiments identical to the element 28. The element 28 can be made from a first section 44 and a second section 46. The first section 44 can be secured to the second section 46. The

sections

44 and 46 can have a section body 48 and an outer layer 50. The section body 48 can be solid, solid with one or more dimples or channels, or hollow. The outer layer 50 can be a porous membrane or have macroscopic holes or channels that are in communication with the section body 48. The element 28 can have one or more leader channels 52 having leader channel diameters 54 about equal to or greater than the leader diameter 34. The leader channels 52 can be fixed to the leader 26. Alternatively, the leader 26 can have a clearance with the leader channels 52. A ferrule 56 can be fixed to the leader 26. The ferrule 56 can be locked with an interference fit into a ferrule cavity 58.

FIGS. 6 and 7 illustrate an embodiment of the first section 44 and the element 28, respectively. FIGS. 8 and 9 illustrate another embodiment of the first section 44 and the element 28, respectively. In the embodiments shown in FIGS. 6-9, the

sections

44 and 46 can be identically shaped. In the embodiments in FIGS. 4-7, the

sections

44 and 46 can be shaped to fit the

opposite section

44 or 46 and form an interference fit, for example a snap lock, with the

opposite section

44 or 46. The interference fit minimizes movement of the

sections

44 and 46 with respect to each other in any direction. In the embodiments in FIGS. 8 and 9, the

sections

44 and 46 can be shaped to fit the

opposite section

44 or 46 and form an interference fit that allows movement of the

sections

44 and 46 with respect to each other in one translational direction.

FIG. 10 illustrates a segment of an embodiment of the device 24 with the leaders 26 having first ends 60 and second ends 62 that can be integrated and conjoined segments of the

elements

28, 30 and 32. The leaders 26 can be preformed resilient structures formed into helical shapes. The device 24 can be made entirely from the leader 26 and without

elements

28, 30 and 32, as illustrated in FIG. 11, or each

element

28, 30 or 32 can be separated from the

adjacent elements

28, 30 and 32 by as few as about 0.5 turns of the leader 26. More narrowly, each

element

28, 30 or 32 can be separated from the

adjacent elements

28, 30 and 32 by from about 2 turns to about 3 turns of the leader 26. The leaders 26 can have a preformed leader depth 64 from about 0.25 mm (0.0098 in.) to about 2.0 mm (0.079 in.), more narrowly from about 0.5 mm (0.02 in.) to about 1.0 mm (0.039 in.), and a preformed leader width 66 from about 0.5 mm (0.02 in.) to about 4.0 mm (0.16 in.), more narrowly from about 1.0 mm (0.039 in.) to about 2.0 mm (0.079 in.). The leaders 26 can also have wind lengths 68. The wind lengths 68 can be the longitudinal component of the length covered by about 360 degrees of helical turn in the

element

28, 30 or 32. The wind lengths 68 can be about 2.0 mm (0.079 in.). The wind lengths 68 can also vary within a

single element

28, 30 or 32, and five wind lengths 68 can be about 1.0 cm (0.39 in.).

The device 24 can be structurally reinforced. For example, a structural reinforcement 70 can be integrated onto the surface or encased by the leader 26 and/or the

elements

28, 30, and 32. The reinforcement can be a polyester weave, or a coil or spiral element, for example a continuous wire wound within the device 24 such that the reinforcement 70 parallels the coils or helical shapes of the

conjoined elements

28, 30 and 32 of the device 24.

In other embodiments of the device 24 illustrated in FIGS. 12a-c , the leaders 26 can have a male interference-fit piece, for example brads or poppets 72, on a first end 60 of the leaders 26. The second ends 62 of the leaders 26 can be integrated and conjoined with the

elements

28, 30 and 32. The

elements

28, 30 and 32 can have female interference-fit pieces, for example plugs or sockets 74, integrated into the

elements

28, 30 and 32 at the opposite ends of the

elements

28, 30 and 32 from the poppets 74. The poppets 72 and sockets 74 can be shaped and sized to attach to each other with a sufficient interference fit to impede removal of the poppets 72 from the sockets 74. The

elements

28 and 30 at open ends 76 of the device 24 do not attach to a neighboring

element

28, 30 and 32. The

elements

28 and 30 at the open ends 76 can lack the poppet 72 or the socket 74 on the open ends 76 of the

elements

28 and 30.

In another embodiment of the device 24 illustrated in FIG. 13, the first end 60 of the leader 26 can have a first male interference-fit piece, for example a first poppet 72 a, and the second end 62 of the leader 26 can have a second male interference-fit piece, for example a second poppet 72 b. A leader with male interference-fit pieces at two ends can be called a “dogbone”. The

elements

28, 30 and 32 can have two female interference-fit pieces, for example sockets 74, integrated into opposite ends of each

element

28, 30 and 32.

FIG. 14 illustrates a segment of an embodiment of the device 24 having first leaders 26 a with ends 60 and 62 that can be integrated and conjoined segments of the

elements

28 and 30 and a second leader 26 b that can pass through the first leaders 26 a and the

elements

28 and 30. The second leader 26 b can have an interference fit at one open end 76, for example a knot 78. The second leader 26 b can be fixed or slidably attached to the

elements

28 and 30.

Radiopaque materials known to one having ordinary skill in the art can be used anywhere in or on the device 24. Examples of radiopaque materials are barium, sulfate, titanium, stainless steel, nickel-titanium alloys (e.g., NiTi), and gold. The ferrule 56 can be made from radiopaque materials. A radiopaque patch or contrast agent can also be integrated into or placed on the leader 26 or the

elements

28, 30, and 32. The contrast agent can be permanent or can be adapted to extravagate over time post-implantation. A radiopaque fiber can be wound integrally with the leader 26. The radiopaque element can be present in a quantity sufficient to allow the operator to view deployment of the device 24 upon delivery, but not sufficient to obstruct the visualization of adjacent tissues and structures post-implantation. For example, upon deployment, the operator can visualize the initial placement and nesting of the

elements

28, 29 and 30 and/or the leader 26, but post-implantation the visualization of the prosthesis 8 can be unobstructed by the radiopaque nature of the

elements

28, 29 and 30 and/or the leader 26

The

elements

28, 30 or 32 can be filled or coated with an agent delivery matrix known to one having ordinary skill in the art and/or a therapeutic and/or diagnostic agent. The device 24, or any of the parts of the device 24, can be coated with the agents. These agents can include radioactive materials; radiopaque materials, for example gold; thrombogenic agents, for example polyurethane, cellulose acetate polymer mixed with bismuth trioxide, and ethylene vinyl alcohol; lubricious, hydrophilic materials; phosphor cholene; anti-inflammatory agents, for example non-steroidal anti-inflammatories (NSAIDs) such as cyclooxygenase-1 (COX-1) inhibitors (e.g., acetylsalicylic acid, for example ASPIRIN® from Bayer AG, Leverkusen, Germany; ibuprofen, for example ADVIL® from Wyeth, Collegeville, Pa.; indomethacin; mefenamic acid), COX-2 inhibitors (e.g., VIOXX® from Merck & Co., Inc., Whitehouse Station, N.J.; CELEBREX® from Pharmacia Corp., Peapack, N.J.; COX-1 inhibitors); immunosuppressive agents, for example Sirolimus (RAPAMUNE®, from Wyeth, Collegeville, Pa.), or matrix metalloproteinase (MMP) inhibitors (e.g., tetracycline and tetracycline derivatives) that act early within the pathways of an inflammatory response. Examples of other agents are provided in Walton et al, Inhibition of Prostoglandin E₂Synthesis in Abdominal Aortic Aneurysms, Circulation, Jul. 6, 1999, 48-54; Tambiah et al, Provocation of Experimental Aortic Inflammation Mediators and Chlamydia Pneumoniae, Brit. J. Surgery 88 (7), 935-940; Franklin et al, Uptake of Tetracycline by Aortic Aneurysm Wall and Its Effect on Inflammation and Proteolysis, Brit. J. Surgery 86 (6), 771-775; Xu et al, Sp1 Increases Expression of Cyclooxygenase-2 in Hypoxic Vascular Endothelium, J. Biological Chemistry 275 (32) 24583-24589; and Pyo et al, Targeted Gene Disruption of Matrix Metalloproteinase-9 (Gelatinase B) Suppresses Development of Experimental Abdominal Aortic Aneurysms, J. Clinical Investigation 105 (11), 1641-1649 which are all incorporated by reference in their entireties. Once the device 24 is deployed, these agents can provide various benefits such as i) promote fusing of the space-occupying

elements

28, 30 or 32 to each other or to the surrounding biologic materials (e.g., a collagen coating), and/or ii) promote a thrombogenic response within the sac 10 to stabilize the device 24 and the prosthesis 8, and/or iii) function to promote healing of the aneurysm at the cellular level such as in the case of treating an inflammatory response.

Method of Making

The

elements

28, 30 and 32 and the leader 26 can be made from methods known to those having ordinary skill in the art. For example, the

elements

28, 30 and 32 can be molded or machined. The embodiments of the device 24 illustrated in FIGS. 10, 11 and 14 can be extruded and then a helical cut in the extrusion can be made by a blade, laser, water jet or hot wire to form the

leaders

26 and 26 a.

The

elements

28, 30 and 32 can be molded, machined, or mounted onto the leader 26. The

elements

28, 30 and 32 can be mounted to the leader 26 with an interference fit, for example by tying knots in the leader 26 surrounding the

elements

28, 30 and 32 mounting the

elements

28, 30 and 32 onto the ferrule 56 which is already crimped onto the leader 26. The

elements

28, 30 and 32 can be pressure fitted onto the leader 26, for example by crimping the

elements

28, 30 and 32 onto the leader 26, snapping snap-

together sections

44 and 46 onto the leader 26, or distortion mounting by heating the

elements

28, 30 and 32 to a threshold of thermal distortion. The

elements

28, 30 and 32 can be glued onto the leader 26 with a biocompatible adhesive (e.g., cyanoacrylate); bonded ultrasonically; or heat bonded (e.g., melting, heat welding). Each

section

44 or 46 can be attached to the

other section

44 or 46 with any of the above methods.

Any part of the device 24, or the device 24 as a whole after assembly, can be coated by dip-coating or spray-coating methods known to one having ordinary skill in the art. One example of a method used to coat a medical device for vascular use is provided in U.S. Pat. No. 6,358,556 by Ding et al. and hereby incorporated by reference in its entirety. Time release coating methods known to one having ordinary skill in the art can also be used to delay the release of an agent in the coating, for example inclusion of a collagen matrix in the coating.

Method of Use

Before using the device 24, the sac 10 can be cleaned of debris (e.g., thrombi), for example by mechanically macerating the debris or using a lytic agent (e.g., Urokinase, for example Abbokinase® from Abbott Laboratories, Abbott Park, Ill.). Examples of devices capable of performing pharmomechanical treatment—that can be delivered to the sac 10 through the same delivery apparatus as the device 24—are the TRELLIS™ and FINO™ from Bacchus Vascular, Inc. (Santa Clara, Calif.). Use of the device 24 can be performed while using a visualization tool, for example fluoroscopy or computed tomography (CT) scanning. The volume of the sac 10 not filled by debris can be estimated from visual inspection, for example by inspection of images from the visualization tool. Software known to one having ordinary skill in the art can also be used to assist in estimating the volume of the sac 10.

A length of the device 24 can be stored in a sterile package, for example by an individual predetermined length or on a spool, spindle, or in a cartridge. The device volume can be reduced by removing more than enough of the device 24 from the sterile package and then reducing the length of the device 24, for example by cutting the leader 26 or unplugging a poppet 72 from a socket 74. In this way, the device volume can be reduced to the approximate volume of the sac 10 not filled by debris. The device volume can be large enough to substantially fill the vascular site, and the device volume can be small enough to prevent substantial alteration of the natural fluid flow through the prosthesis 8.

The device 24 can be deployed to the sac 10 using a trans-graft, trans-collateral, trans-sac, or endoluminal procedure. As illustrated in FIG. 15, a catheter 80 with a distal exit 82 can be placed in the aneurysm 4. The distal exit can be placed at the sac 10. The device 24 can then be passed through the catheter 80 and distal exit 82, and can be deployed into the sac 10.

As illustrated in FIG. 16, a catheter clearance 84 is the distance between the device 24 and an inner wall 86 of the catheter 80. The inner walls 86 of the catheter 80 can act as a guide for the device 24 during deployment. If the catheter clearance 84 is too large, the inner walls 86 of the catheter 80 can no longer act as a guide and the device 24 can “boxcar” within the catheter 80. Boxcarring occurs when the

elements

28, 30 and 32 bunch up and impair delivery, preventing an upstream element from transmitting force to a downstream element in a direction substantially parallel with the inner walls 86. The maximum catheter clearance 84 before the

elements

28, 30 and 32 can begin to boxcar is the “critical clearance”. The critical clearance can be about 80% of the element outer diameter 38, more narrowly about 26% of the element outer diameter, yet more narrowly about 12% of the element outer diameter 38.

An end of the catheter 80 can have a valve 87 to minimize or completely prevent backflow of body fluids or other leakage and improve the connection of other devices to the end of the catheter 80. Use of the valve 87 at the end of the catheter 80 is understood to one having ordinary skill in the art. The valve 87 can be, for example, a hemostasis valve (e.g., from Cook, Inc., Bloomington, Ind.).

FIG. 17 illustrates a ratcheting driver 88 having a feed tube 90 that can be used to control the device 24 during deployment. The device 24 can pass through a channel 92 in the feed tube 90. An end 94 of the feed tube 90 can connect to the valve 87 or the catheter 80. The driver 88 can have a spring-loaded handle 96. The handle 96 can be connected to a ram 98. The handle 96 can move along a track 100 in the feed tube 90. When the handle 96 is pushed, the ram 98 can press the device 24 forward through the channel 92. When the handle 96 is released, the handle 96 can revert to a starting position and prevent the device 24 from moving backwards through the channel 92.

FIG. 18 illustrates a sliding driver 88 having a slider 102. The slider 102, illustrated in FIG. 19, can have a rib 104 that can engage the track 100. The slider 102 can abut and deliver a force to the end of the device 24 when the device 24 is in the channel 92.

The geometries of the

elements

28, 30 and 32 of the device 24 and the properties of the leader 26 can benefit delivery of the device 24. As the slider 102 delivers force to the end of the device 24, the leader 26 can buckle or flex, allowing

elements

28, 30 and 32 to approximate and transmit force from one

element

28, 30 or 32 to the

other elements

28, 30 or 32, thereby giving the device 24 sufficient column strength to move through the channel 92.

As illustrated in FIG. 20, a connector 106 at the end 94 of the feed tube 90 can have a lipped hub 108 and a collar 110. The lipped hub 108 can feed into the valve 87 or the opening of a channel in the catheter 80. The collar 110 can fit over the valve 87 or the end of the catheter 80 that joins with the feed tube 90, or the collar 110 can join with another intermediary device between the catheter 80 or the valve 87 and the feed tube 90. The connector 106 can have a check port 112 in the collar 110.

FIGS. 21-24 illustrate an embodiment of the connector 106 that can lock to, and unlock from, the catheter 80. A first end of the connector 106 can have a latch 114 that can form a friction or interference fit with the valve 87 or the catheter 80 (not shown) when the valve 87 or the catheter 80 is loaded into the collar 110 past the latches 114. The latches 114 can be rigidly attached to lever arms 116. The lever arms 116 can be attached to the connector 106 at an attachment location 118 so that the position of the lever arms 114 forces the latches 114 to form the friction or interference fit with the valve 87 or the catheter 80 when no external forces are applied to the lever arms 116. A second end of the lever arm 116 can also have a press tab or button 120.

When a force (shown by arrows in FIG. 22) is applied to the buttons 120, the lever arms 116 can rotate around the attachment location 118, removing the friction or interference fit between the latches 114 and the valve 87 or the catheter 80.

The connector 106 can have a lock 122 that can be rotatably attached to the remainder of the connector 106. Tabs 124 can protrude from the lock 122. The tabs 124 can be used to aid rotation (shown by arrows in FIGS. 21 and 23) of the lock 122 relative to the remainder of the connector 106, and to provide an interference fit to prevent the lock 122 from turning from one lever arm 114 past the next lever arm 114. The lock 122 can have a thick portion 126 and a thin portion 128.

The lock 122 can be rotated to position the thick portion 126 between the lever arms 116 and a retaining wall 130 (shown in FIGS. 23 and 24), minimizing the rotation of the lever arms 116 and preventing the removal of the friction or interference fit between the latches 114 and the valve 87 or the catheter 80. With the lock 122 in this position, the valve 87 or the catheter 80 can be locked to the connector 106.

The lock 122 can be rotated to position the thin portion 128 between the lever arms 116 and the retaining wall 130 (shown in FIGS. 21 and 22), allowing substantially free rotation of the lever arms 116 and enabling removal of the friction or interference fit between the latches 114 and the valve 87 or the catheter 80. With the lock 122 in this position, the valve 87 or the catheter 80 can be unlocked and removed from the connector 106.

The driver 88 can be integrated with the sterile package (e.g., individual predetermined length, spool, spindle, or cartridge) loaded with the device 24. A new package loaded with the device 24 can replace or be swapped for an old package at the connector 106.

The device 24 can be visualized by the visualization tool before, during and after the device 24 has been deployed. After the device 24 has been deployed, any agents in or on the device 24 can elute into the tissue and fluids. The vascular prosthetic 8 can be implanted before, during or after the device 24 is deployed.

It is apparent to one skilled in the art that various changes and modifications can be made to this disclosure, and equivalents employed, without departing from the spirit and scope of the invention.

Claims

We claim:

1. A system for treating an aneurysm comprising:

a catheter having a distal exit having a deployed configuration and an undeployed configuration; and

a self-fusing material,

wherein when the self-fusing material is in the undeployed configuration, the distal exit is placed between an outer surface of a prosthesis and a wall of the aneurysm, and the self-fusing material is in the catheter,

wherein when the self-fusing material is in a deployed configuration, the self-fusing material is in the space between the outer surface of the prosthesis and the wall of the aneurysm, and the self-fusing material has fused to itself, promoting a thrombogenic response within the aneurysm to stabilize the self-fusing material and the prosthesis,

wherein the self-fusing material is configured to promote fusing or other coagulative effect, and

wherein the self-fusing material is radiopaque such that in the deployed configuration, the visualization of the prosthesis is unobstructed by the radiopaque nature of the self-fusing material.

2. The system of claim 1, wherein the self-fusing material comprises a polymer formulation.

3. The system of claim 1, wherein at the distal exit of the catheter, the catheter comprises a valve to minimize or completely prevent backflow of body fluids or other leakage.

4. The system of claim 1, further comprising a visualization tool for visualizing the self-fusing material before, during, and after the self-fusing material has been deployed.

5. The system of claim 1, wherein the self-fusing material comprises a coating, wherein the coating is an agent, and wherein the agent is at least one of a therapeutic agent and a diagnostic agent.

6. A system for treating an aneurysm comprising:

a self-fusing material,

wherein when the self-fusing material is in an undeployed configuration, the distal exit is placed between an outer surface of a prosthesis and a wall of the aneurysm, and the self-fusing material is in the catheter,

wherein when the self-fusing material is in a deployed configuration, the self-fusing material is in the space of the aneurysm, and the self-fusing material has fused to itself, promoting a thrombogenic response within the aneurysm to stabilize the self-fusing material,

wherein at the distal exit of the catheter, the catheter comprises a valve to minimize or completely prevent backflow of body fluids or other leakage.

7. The system of claim 6, wherein the self-fusing material comprises a polymer formulation.

8. The system of claim 6, wherein at the distal exit of the catheter, the catheter comprises a valve to minimize or completely prevent backflow of body fluids or other leakage.

9. The system of claim 6, further comprising a visualization tool that can visualize the self-fusing material before, during, and after the self-fusing material has been deployed.

10. A method for treating an aneurysm comprising:

placing a distal exit of a catheter between an outer surface of a prosthesis and a wall of the aneurysm; and

deploying a self-fusing material through the distal exit of the catheter;

wherein after the self-fusing material is fully deployed from the catheter, the self-fusing material fuses with itself, promoting a thrombogenic response within the aneurysm to stabilize the self-fusing material,

11. The method of claim 10, wherein the self-fusing material comprises a polymer formulation.

12. The method of claim 10, wherein the self-fusing material is deployed within the space of the aneurysm using a trans-graft, trans-collateral, trans-sac, or endoluminal procedure.

13. The method of claim 10, further comprising visualizing an initial placement and nesting of the self-fusing material prior to and during deployment with a visualization tool.

14. The method of claim 10, wherein at the distal exit of the catheter, the catheter comprises a valve to minimize or completely prevent backflow of body fluids or other leakage.

15. The method of claim 10, wherein placing the distal exit of the catheter between the outer surface of the prosthesis and the wall of the aneurysm comprises placing the distal exit of the catheter within a space of the aneurysm, wherein the space of the aneurysm is between the outer surface of the prosthesis and the wall of the aneurysm.

16. The method of claim 15, wherein the self-fusing material is radiopaque such that after the self-fusing material has been deployed, the visualization of the prosthesis is unobstructed by the radiopaque nature of the self-fusing material.

17. The method of claim 15, further comprising selecting the self-fusing material having a proper volume so that the self-fusing material is large enough to substantially fill a void in the aneurysm, yet small enough to prevent substantial alteration of a natural fluid flow through the prosthesis.

18. The method of claim 15, wherein the self-fusing material is deployed between the outer surface of the prosthesis and the wall of the aneurysm using a trans-graft, trans-collateral, trans-sac, or endoluminal procedure.

19. The method of claim 15, wherein the self-fusing material comprises a polymer formulation.

20. The method of claim 10, further comprising visualizing the self-fusing material before, during, and after the self-fusing material has been deployed.